System and method of establishing a protocol for providing electrical stimulation with a stimulation system to treat a patient

ABSTRACT

A computer-assisted stimulation programming of an implantable medical device is performed. A perception threshold is determined for a plurality of contacts on a lead configured to be implanted inside a patient. The perception threshold is determined by automatically performing a first sweep of the plurality of contacts and automatically performing a second sweep of a stimulation parameter. A paresthesia coverage provided by the plurality of contacts is determined by automatically performing a third sweep of the plurality of contacts and automatically performing a fourth sweep of the stimulation parameter. The fourth sweep is performed based on the determined perception thresholds. The first sweep, the second sweep, the third sweep, and the fourth sweep are performed without needing a manual input from a human user. A subset of the contacts corresponding to the paresthesia coverage is selected. In response to user input, stimulation programming is performed using the subset of contacts.

PRIORITY DATA

The present application is a continuation application of U.S. patent application Ser. No. 13/118,764, filed on May 31, 2011, now U.S. Pat. No. 9,144,680 issued Sep. 29, 2015, the disclosure of which is hereby incorporated by reference in its entirety.

BACKGROUND

The invention relates to a stimulation system, such as a spinal cord stimulation (SCS) system, having a tool for programming an electrical stimulation generator, such as an implantable pulse generator (IPG), of the system. The invention also relates to a method for developing a protocol for the stimulation system.

A spinal cord stimulator is a device used to provide electrical stimulation to the spinal cord or spinal nerve neurons for managing pain. The stimulator includes an implanted or external pulse generator and an implanted medical electrical lead having one or more electrodes at a distal location thereof. The pulse generator provides the stimulation through the electrodes via a body portion and connector of the lead. Spinal cord stimulation programming is defined as the discovery of the stimulation electrodes and parameters that provide the best possible pain relief (or paresthesia) for the patient using one or more implanted leads and its attached IPG. The programming is typically achieved by selecting individual electrodes and adjusting the stimulation parameters, such as the shape of the stimulation waveform, amplitude of current in mA (or amplitude of voltage in V), pulse width in microseconds, frequency in Hz, and anodic or cathodic stimulation.

With newer medical electrical leads having an increased number of electrodes, the electrode and parameter combination increases exponentially. This results in a healthcare professional, such as a clinician, requiring a substantial amount of time for establishing a manually created protocol for providing therapeutic spinal cord stimulation. Therefore, a manual approach for creating a protocol is not an optimal solution for the SCS system.

SUMMARY

Numerous embodiments of the invention provide a method and system for programming an SCS system with a substantially reduced time requirement and increased accuracy. More specifically, in numerous embodiments, a sweep process is used with the electrodes of an implanted medical lead to determine the proper SCS program (also referred to herein as an SCS protocol) for providing the best possible pain relieve for the patient.

In one embodiment, the invention provides a programming device for establishing a protocol for a plurality of electrodes in one or more medical leads coupled to an electrical stimulation generator. The programming device is adapted to be in communication with the electrical stimulation generator and a patient feedback device. The programming device includes, a first communication port for communication with the electrical stimulation generator, a second communication port for communication with the patient feedback device, a user interface; and a controller coupled to the first communication port, the second communication port, and the user interface. The controller is configured to create the protocol for providing electrical stimulation to treat the patient.

In another embodiment, the invention provides a system for providing therapeutic electrical stimuli to a patient. The system includes one or more implantable medical leads having a plurality of electrodes, an electrical stimulation generator coupled to the lead, a patient feedback device, and a programming device in communication with the electrical stimulation generator and in communication with the patient feedback device. The programming device configured to initiate a first automated and systematic sweep through the plurality of electrodes to determine a respective perception threshold associated with each electrode, receive from the patient feedback device whether the patient provided feedback while performing the first automated and systematic sweep, initiate a second automated and systematic sweep through the plurality of electrodes to determine an electrode that is associated with a pain area of the patient, receive from the patient feedback device whether the patient provided feedback while performing the second automated and systematic sweep, and develop the protocol for providing therapeutic electrical stimulation to treat the patient based on the second automated and systematic sweep and the detected patient feedback. The second automated and systematic sweep uses the respective perception thresholds from the first automated and systematic sweep.

In another embodiment, the invention provides a patient feedback device for providing feedback to a programming device of an electrical stimulation system providing therapeutic stimulation. The patient feedback device includes a sensor supported by the ergonomic housing. The sensor receives a physical response from the patient and provides an electrical signal in response thereto. The patient feedback device further includes a controller supported by the housing and coupled to the sensor and a communication port supported by the housing and coupled to the controller. The controller receives the electrical signal and initiates a communication signal in response thereto. The communication port receives the communication signal and transmits the communication signal to the programming device.

Other aspects of the invention will become apparent by consideration of the detailed description and accompanying drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a partial perspective view of a patient using a spinal cord stimulation system.

FIG. 2 is a perspective view of an in-line lead for use in the spinal cord stimulation system of FIG. 1.

FIG. 3 is a perspective view of a paddle lead for use in the spinal cord stimulation system of FIG. 1.

FIG. 4 is a block diagram of a patient-feedback device for use in the spinal cord stimulation system of FIG. 1.

FIG. 5 is a side view of a patient-feedback device inserted in the mouth of a patient.

FIG. 6 is a side view of a patient-feedback device with optical sensing.

FIG. 7 is a side view of a patient-feedback device activated by a foot of a patient.

FIG. 8 is a block diagram of an implantable pulse generator for use in the spinal cord stimulation system of FIG. 1.

FIG. 9 is a block diagram of a clinician programmer for use in the spinal cord stimulation system of FIG. 1.

FIG. 10 is a flow diagram of a patient performing an initial visit with a clinician.

FIG. 11 is a flow diagram of a patient undergoing an initial visit followed by trial surgery procedure.

FIG. 12 is a flow diagram of the manual programming of a lead.

FIG. 13 is a flow diagram of the computer assisted programming of a lead.

FIG. 14 is a flow diagram of a patient performing a post trial programming session.

FIG. 15 is a flow diagram of a patient undergoing a permanent surgery procedure.

FIG. 16 is a flow diagram of an exemplary computer assisted stimulation programming process for use with the spinal cord stimulation system of FIG. 1.

FIG. 17 is a flow diagram of an exemplary process for determining impedance values associated with each electrode.

FIGS. 18A and 18B are a flow diagram of an exemplary process for determining perception threshold values associated with each electrode.

FIG. 19 is a flow diagram of an exemplary process for determining a stimulation electrode sub-array reaching a pain area of the patient.

DETAILED DESCRIPTION

Before any embodiments of the invention are explained in detail, it is to be understood that the invention is not limited in its application to the details of construction and the arrangement of components set forth in the following description or illustrated in the following drawings. The invention is capable of other embodiments and of being practiced or of being carried out in various ways.

The invention herein relates to an electrical stimulation system for providing stimulation to target tissue of a patient. The system described in detail below is a spinal cord stimulation (SCS) system for providing electrical pulses to the neurons of the spinal cord of a patient. However, many aspects of the invention are not limited to spinal cord stimulation. The electrical stimulation system may provide stimulation to other body portions including a muscle or muscle group, nerves, the brain, etc.

FIG. 1 shows a spinal cord stimulation system 100 in use with a patient 105. The system includes one or more implanted medical electrical leads 110 connected to an implantable pulse generator (IPG) 115. The leads 110 include an electrode array 120 at a distal end of the base lead cable. The electrode array 120 includes one or more electrical stimulation electrodes (may also be referred as electrode contacts or simply electrodes) and is placed adjacent to the dura of the spine 125 using an anchor. The spinal column includes the C1-C7 (cervical), T1-T12 (thoracic), L1-L5 (lumbar) and S1-S6 (sacral) vertebrae and the electrode array(s) 120 may be positioned anywhere along the spine 125 to deliver the intended therapeutic effects of spinal cord electrical stimulation in a desired region of the spine. The electrodes (discussed further in FIGS. 2 and 3) of the electrode arrays 120 promote electrical stimulation to the neurons of the spine based on electrical signals generated by the IPG 115. In one construction, the electrical signals are regulated current pulses that are rectangular in shape. However, the electrical signals can be other types of signals, including other types of pulses (e.g., regulated voltage pulses), and other shapes of pulses (e.g., trapezoidal, sinusoidal). The stimulation is provided from the IPG 115 to the electrodes via the base lead, which is connected to the IPG 115 with the proximal end of the base lead. The body of the lead can traverse through the body of the patient via the spinal column and from the spinal column through the body of the patient to the implant site of the IPG 115.

The IPG 115 generates the electrical signals through a multiplicity of electrodes (e.g., four, eight, sixteen, twenty-four electrodes). The IPG 115 can control six aspects of electrical stimulation based on a protocol (may also be referred to as a program): on/off, amplitude (e.g., current or voltage), frequency, pulse width, pulse shape, and polarity (anodic or cathodic stimulation). The stimulation most discussed herein is a regulated (or constant) current that provides a square wave, cathodic stimulation with a variable amplitude, frequency, and/or pulse width. Typically, the IPG 115 is implanted in a surgically made pocket (e.g., in the abdomen) of the patient. However, the pulse generator can also be an external pulse generator (EPG).

The IPG 115 communicates with any one of a clinician programmer (CP) 130, a patient programmer and charger (PPC) 135, and a pocket (or fob) programmer (PP) 140. As discussed in further detail below, the CP 130 interacts with the IPG 115 to develop a protocol for stimulating the patient. The developing of the protocol is assisted with the use of a patient-feedback device (PFD) 145. Once a protocol is developed, the PPC 135 or the PP 140 can activate, deactivate, or perform limited changes to the programming parameters of the protocol. The protocol may be stored at the IPG 115 or can be communicated and stored at the PPC 135 or the PP 140. The PPC 135 is also used for charging the IPG 115.

For the construction described herein, the IPG 115 includes a rechargeable, multichannel, radio-frequency (RF) programmable pulse generator housed in a metallic (e.g., titanium) case or housing. The metallic case is sometimes referred to as the “can” and may act either as a cathode or an anode or floating to the electrical contacts.

Referring now to FIGS. 2 and 3, the figures show two exemplary leads 110A and 110B, respectively, that can be used in the SCS system. A first common type of lead 110 is the “in-line” lead shown in FIG. 2. An in-line lead 110A includes individual electrodes 150A along the length of a flexible cable 155A. A second common type of lead 110 is the “paddle” lead shown in FIG. 3. In general, the paddle lead 110B is shaped with a wide platform 160B on which a variety of electrode 150B configurations are situated. For example, the paddle lead 110B shown in FIG. 3 has two columns of four rectangular shaped electrodes 150B. A paddle lead typically contains contacts on one side only, but is not restricted to individual electrodes on either side, or electrodes perforating the carrier material.

For both leads shown in FIGS. 2 and 3, a flexible cable 155A or 155B has respective small wires for the electrodes 150A or 150B. The wires are embedded within the cable 155A or 155B and carry the electrical stimulation from the IPG 115 to the electrodes 150A or 150B.

It is envisioned that other types of leads 110 and electrode arrays 120 can be used with the invention. Also, the number of electrodes 150 and how the electrodes 150 are arranged in the electrode array 120 can vary from the examples discussed herein.

The leads shown in FIGS. 2 and 3 are multiple channel leads. Here, a “channel” is defined as a specified electrode 150, or group of electrodes 150, that receives a specified pattern or sequence of electrical stimuli. For simplicity, this description will focus on each electrode 150 and the IPG's 115 metallic housing providing a respective channel. When more than one channel is available, each channel may be programmed to provide its own stimulus to its defined electrode.

There are many instances when it is advantageous to have multiple channels for stimulation. For example, different pain locations (e.g., upper extremities, lower extremities) of the patient may require different stimuli. Further, some patients may exhibit conditions better suited to “horizontal” stimulation paths, while other patients may exhibit conditions better suited to “vertical” stimulation paths. Therefore, multiple electrodes positioned to provide multiple channels can cover more tissue/neuron area, and thereby provide better stimulation protocol flexibility to treat the patient.

It is also envisioned that the number of leads 110 can vary. For example, one, two, or four leads 110 can be connected to the IPG 115. The electrode arrays 120 of the leads 110, respectively, can be disposed in different vertical locations on the spine 125 with respect to a vertical patient 105, can be disposed horizontally (or “side-by-side”) on the spine 125 with respect to a vertical patient 105, or some combination thereof.

In alternative to the IPG 115, the leads 110 can receive electrical stimuli from an external pulse generator (EPG) (also referred to a trial stimulator) through one or more percutaneous lead extensions. An EPG may be used during a trial period.

For the specific construction and operation described herein, a single lead 110 having a two-by-four electrode paddle (as shown in FIG. 3) is secured to the thoracic portion of the spine 125. An IPG 115 having a metallic housing is disposed within the patient 105. The housing acts as another electrode in this contemplated SCS system 100. Thus, this arrangement results in nine electrodes total. Also, the specifically-discussed system includes nine channels formed by the eight electrodes of the electrode array 120, respectively, and the metallic housing of the IPG 115. However, it contemplated that a different number of leads, electrodes, and channels fall within the scope of the invention.

Referring back to FIG. 1, a user provides feedback to the CP 130 with a PFD 145 while the CP 130 develops the protocol for the IPG 115. In FIG. 1, the PFD 145 is an ergonomic handheld device having a sensor (also referred to as input) 165, a controller, and a communications output 175. The sensor 165 can take the form of a discrete switch or can take the form of a continuously variable input, such as through the use of a strain gauge. It is envisioned that the use of a continuously variable input can provide magnitude information, thereby providing feedback information.

FIG. 4 provides a block diagram of an exemplary handheld PFD 145 used in the SCS system 100. The PFD 145 includes two inputs 900 and 905 in communication with the housing of the device 145 and one input 910 internal to the housing. One of the external inputs 900 is a binary ON/OFF switch, preferably activated by the patient's thumb, to allow the patient 105 to immediately deactivate stimulation. The second input 905 includes a force or displacement sensor sensing the pressure or force exerted by the patient's hand. The sensed parameter can be either isotonic (constant force, measuring the distance traversed) or isometric (measuring the force, proportional to pressure applied by patient 105). The resulting signal from the sensor 905 is analog and, therefore, the signal is conditioned, amplified, and passed to a microcontroller via an analog-to-digital converter.

The internal input 910 for the PFD 145 of FIG. 4 is a motion sensor. The sensor 910, upon detecting motion, initiates activation of the PFD 145. The device 145 stays active until movement is not detected by the sensor 910 for a time period. Power is provided by an internal battery 920 that can be replaceable and/or rechargeable.

The processing of the inputs from the sensors 900 and 905 take place in a controller, such as a microcontroller 925. The microcontroller 925 includes a suitable programmable portion 930 (e.g., a microprocessor or a digital signal processor), a memory 935, and a bus 940 or other communication lines. Output data of the microcontroller 925 is sent via a Bluetooth bi-direction radio communication portion 945 to the CP 130. The Bluetooth portion 945 includes a Bluetooth communication interface, an antenna switch, and a related antenna, all of which allows wireless communication following the Bluetooth Special Interest Group standard. Other outputs may include indicators (such as light-emitting diodes) for communicating stimulation activity 950, sensor activation 955, and device power 960, and a speaker and related circuitry 965 for audible communication.

As discussed further below, the patient 105 provides feedback to the SCS system 100, and specifically the CP 130, while the CP 130 establishes the protocol for the IPG 115. The patient 105 can activate the PFD 145 when the patient 105 feels various stimuli, such as paresthesia or pain.

FIGS. 5-7 provide other means for receiving patient feedback. More specifically, FIG. 5 shows a mouth-piece 180 that is inserted into the mouth of the patient. The user provides feedback by biting the mouthpiece. FIG. 6 shows an optical sensor 185 (such as a camera and related image processing software) that detects visual cues from a patient. An example visual cue may be the blinking of the patient's eyes. FIG. 7 shows a foot pedal 190 that receives input by the patient manipulating a switch with his foot. It is also envisioned that the patient may provide feedback directly through the touch screen or hard buttons on the CP 130.

As discussed earlier, it should be understood that aspects of the SCS system 110 can be applied to other types of electrical stimulation systems. That is, other electrical stimulation systems provide electrical stimuli to other types of target tissues. Similar to the SCS system 110, these other electrical stimulation systems include one or more medical electrical leads having electrodes, a stimulation generator coupled to the one or more medical electrical leads, and a clinician programmer for establishing a protocol with the stimulation generator.

FIG. 8 shows a block diagram of one construction of the IPG 115. The IPG 115 includes a printed circuit board (“PCB”) that is populated with a plurality of electrical and electronic components that provide power, operational control, and protection to the IPG 115. With reference to FIG. 8, the IPG 115 includes a communication portion 200 having a transceiver 205, a matching network 210, and antenna 212. The communication portion 200 receives power from a power ASIC (discussed below), and communicates information to/from the microcontroller 215 and a device (e.g., the CP 130) external to the IPG 115. For example, the IPG 115 can provide bi-direction radio communication capabilities, including Medical Implant Communication Service (MICS) bi-direction radio communication following the MICS specification.

The IPG 115, as previously discussed, provides stimuli to electrodes 150 of an implanted medical electrical lead 110. As shown in FIG. 8, N electrodes 150 are connected to the IPG 115. In addition, the enclosure or housing 220 of the IPG 115 can act as an electrode. The stimuli are provided by a stimulation portion 225 in response to commands from the microcontroller 215. The stimulation portion 225 includes a stimulation application specific integrated circuit (ASIC) 230 and circuitry including blocking capacitors and an over-voltage protection circuit. As is well known, an ASIC is an integrated circuit customized for a particular use, rather than for general purpose use. ASICs often include processors, memory blocks including ROM, RAM, EEPROM, Flash, etc. The stimulation ASIC 230 can include a processor, memory, and firmware for storing preset pulses and protocols that can be selected via the microcontroller 215. The providing of the pulses to the electrodes 150 is controlled through the use of a waveform generator and amplitude multiplier of the stimulation ASIC 230, and the blocking capacitors and overvoltage protection circuitry of the stimulation portion 225, as is known in the art. The stimulation portion 225 of the IPG 115 receives power from the power ASIC (discussed below). The stimulation ASIC 230 also provides signals to the microcontroller 215. More specifically, the stimulation ASIC 230 can provide impedance values for the channels associated with the electrodes 150, and also communicate calibration information with the microcontroller 215 during calibration of the IPG 115.

The IPG 115 also includes a power supply portion 240. The power supply portion includes a rechargeable battery 245, fuse 250, power ASIC 255, recharge coil 260, rectifier 263 and data modulation circuit 265. The rechargeable battery 245 provides a power source for the power supply portion 240. The recharge coil 260 receives a wireless signal from the PPC 135. The wireless signal includes an energy that is converted and conditioned to a power signal by the rectifier 263. The power signal is provided to the rechargable battery 245 via the power ASIC 255. The power ASIC 255 manages the power for the IPG 115. The power ASIC 255 provides one or more voltages to the other electrical and electronic circuits of the IPG 115. The data modulation circuit 265 controls the charging process.

The IPG also includes a magnetic sensor 280. The magnetic sensor 280 provides a “hard” switch upon sensing a magnet for a defined period. The signal from the magnetic sensor 280 can provide an override for the IPG 115 if a fault is occurring with the IPG 115 and is not responding to other controllers.

The IPG 115 is shown in FIG. 8 as having a microcontroller 215. Generally speaking, the microcontroller 215 is a controller for controlling the IPG 115. The microcontroller 215 includes a suitable programmable portion 285 (e.g., a microprocessor or a digital signal processor), a memory 290, and a bus or other communication lines. An exemplary microcontroller capable of being used with the IPG is a model MSP430 ultra-low power, mixed signal processor by Texas Instruments. More specifically, the MSP430 mixed signal processor has internal RAM and flash memories, an internal clock, and peripheral interface capabilities. Further information regarding the MSP 430 mixed signal processor can be found in, for example, the “MSP430G2x32, MSP430G2x02 MIXED SIGNAL MICROCONTROLLER” data sheet; dated December 2010, published by Texas Instruments at its website; the content of the data sheet being incorporated herein by reference.

The IPG 115 includes memory, which can be internal to the control device (such as memory 290), external to the control device (such as serial memory 295), or a combination of both. Exemplary memory include a read-only memory (“ROM”), a random access memory (“RAM”), an electrically erasable programmable read-only memory (“EEPROM”), a flash memory, a hard disk, or another suitable magnetic, optical, physical, or electronic memory device. The programmable portion 285 executes software that is capable of being stored in the RAM (e.g., during execution), the ROM (e.g., on a generally permanent basis), or another non-transitory computer readable medium such as another memory or a disc.

Software included in the implementation of the IPG 115 is stored in the memory 290. The software includes, for example, firmware, one or more applications, program data, one or more program modules, and other executable instructions. The programmable portion 285 is configured to retrieve from memory and execute, among other things, instructions related to the control processes and methods described below for the IPG 115. For example, the programmable portion 285 is configured to execute instructions retrieved from the memory 290 for sweeping the electrodes 150 in response to a signal from the CP 130.

The PCB also includes a plurality of additional passive and active components such as resistors, capacitors, inductors, integrated circuits, and amplifiers. These components are arranged and connected to provide a plurality of electrical functions to the PCB including, among other things, filtering, signal conditioning, or voltage regulation, as is commonly known.

FIG. 9 shows a block diagram of one construction of the CP 130. The CP 130 includes a printed circuit board (“PCB”) that is populated with a plurality of electrical and electronic components that provide power, operational control, and protection to the CP 130. With reference to FIG. 9, the CP includes a processor 300. The processor 300 is a controller for controlling the CP 130 and, indirectly, the IPG 115 as discussed further below. In one construction, the processor 300 is an applications processor model i.MX515 available from Freescale Semiconductor. More specifically, the i.MX515 applications processor has internal instruction and data cashes, multimedia capabilities, external memory interfacing, and interfacing flexibility. Further information regarding the i.MX515 applications processor can be found in, for example, the “IMX510EC, Rev. 4” data sheet; dated August 2010; published by Freescale Semiconductor at its website, the content of the data sheet being incorporated herein by reference. Of course, other processing units, such as other microprocessors, microcontrollers, digital signal processors, etc., can be used in place of the processor 300.

The CP 130 includes memory, which can be internal to the processor 300 (e.g., memory 305), external to the processor 300 (e.g., memory 310), or a combination of both. Exemplary memory include a read-only memory (“ROM”), a random access memory (“RAM”), an electrically erasable programmable read-only memory (“EEPROM”), a flash memory, a hard disk, or another suitable magnetic, optical, physical, or electronic memory device. The processor 300 executes software that is capable of being stored in the RAM (e.g., during execution), the ROM (e.g., on a generally permanent basis), or another non-transitory computer readable medium such as another memory or a disc. The CP 130 also includes input/output (“I/O”) systems that include routines for transferring information between components within the processor 300 and other components of the CP 130 or external to the CP 130.

Software included in the implementation of the CP 130 is stored in the memory 305 of the processor 300, RAM 310, ROM 315, or external to the CP 130. The software includes, for example, firmware, one or more applications, program data, one or more program modules, and other executable instructions. The processor 300 is configured to retrieve from memory and execute, among other things, instructions related to the control processes and methods described below for the CP 130. For example, the processor 300 is configured to execute instructions retrieved from the memory 140 for establishing a protocol to control the IPG 115.

One memory shown in FIG. 9 is memory 310, which can be a double data rate (DDR2) synchronous dynamic random access memory (SDRAM) for storing data relating to and captured during the operation of the CP 130. In addition, a secure digital (SD) multimedia card (MMC) can be coupled to the CP for transferring data from the CP to the memory card via slot 315. Of course, other types of data storage devices can be used in place of the data storage devices shown in FIG. 9.

The CP 130 includes multiple bi-directional radio communication capabilities. Specific wireless portions included with the CP 130 are a Medical Implant Communication Service (MICS) bi-direction radio communication portion 320, a WiFi bi-direction radio communication portion 325, and a Bluetooth bi-direction radio communication portion 330. The MICS portion 320 includes a MICS communication interface, an antenna switch, and a related antenna, all of which allows wireless communication using the MICS specification. The WiFi portion 375 and Bluetooth portion 330 include a WiFi communication interface, a Bluetooth communication interface, an antenna switch, and a related antenna all of which allows wireless communication following the WiFi Alliance standard and Bluetooth Special Interest Group standard. Of course, other wireless local area network (WLAN) standards and wireless personal area networks (WPAN) standards can be used with the CP 130.

The CP 130 includes three hard buttons: a “home” button 335 for returning the CP to a home screen for the device, a “quick off” button 340 for quickly deactivating stimulation IPG, and a “reset” button 345 for rebooting the CP 130. The CP 130 also includes an “ON/OFF” switch 350, which is part of the power generation and management block (discussed below).

The CP 130 includes multiple communication portions for wired communication. Exemplary circuitry and ports for receiving a wired connector include a portion and related port for supporting universal serial bus (USB) connectivity 355, including a Type-A port and a Micro-B port; a portion and related port for supporting Joint Test Action Group (JTAG) connectivity 360, and a portion and related port for supporting universal asynchronous receiver/transmitter (UART) connectivity 365. Of course, other wired communication standards and connectivity can be used with or in place of the types shown in FIG. 9.

Another device connectable to the CP 130, and therefore supported by the CP 130, is an external display. The connection to the external display can be made via a micro High-Definition Multimedia Interface (HDMI) 370, which provides a compact audio/video interface for transmitting uncompressed digital data to the external display. The use of the HDMI connection 370 allows the CP 130 to transmit video (and audio) communication to an external display. This may be beneficial in situations where others (e.g., the surgeon) may want to view the information being viewed by the healthcare professional. The surgeon typically has no visual access to the CP 130 in the operating room unless an external screen is provided. The HDMI connection 370 allows the surgeon to view information from the CP 130, thereby allowing greater communication between the clinician and the surgeon. For a specific example, the HDMI connection 370 can broadcast a high definition television signal that allows the surgeon to view the same information that is shown on the LCD (discussed below) of the CP 130.

The CP 130 includes a touch screen I/O device 375 for providing a user interface with the clinician. The touch screen display 375 can be a liquid crystal display (LCD) having a resistive, capacitive, or similar touch-screen technology. It is envisioned that multitouch capabilities can be used with the touch screen display 375 depending on the type of technology used.

The CP 130 includes a camera 380 allowing the device to take pictures or video. The resulting image files can be used to document a procedure or an aspect of the procedure. For example, the camera 380 can be used to take pictures of barcodes associated with the IPG 115 or the leads 120, or documenting an aspect of the procedure, such as the positioning of the leads. Similarly, it is envisioned that the CP 130 can communicate with a fluoroscope or similar device to provide further documentation of the procedure. Other devices can be coupled to the CP 130 to provide further information, such as scanners or RFID detection. Similarly, the CP 130 includes an audio portion 385 having an audio codec circuit, audio power amplifier, and related speaker for providing audio communication to the user, such as the clinician or the surgeon.

The CP 130 further includes a power generation and management block 390. The power block 390 has a power source (e.g., a lithium-ion battery) and a power supply for providing multiple power voltages to the processor, LCD touch screen, and peripherals.

As best shown in FIG. 1, the CP 130 is a handheld computing tablet with touch screen capabilities. The tablet is a portable personal computer with a touch screen, which is typically the primary input device. However, an external keyboard or mouse can be attached to the CP 130. The tablet allows for mobile functionality not associated with even typical laptop personal computers.

In operation, the IPG 115 (which may also be an EPG) through the use of the implanted medical electrical leads 110, and specifically the electrodes 150, stimulates neurons of the spinal cord 125. The IPG 115 selects an electrode stimulating configuration, selects a stimulation waveform, regulates the amplitude of the electrical stimulation, controls the width and frequency of electrical pulses, and selects cathodic or anodic stimulation. This is accomplished by a healthcare professional (e.g., a clinician), using the CP 130, setting the parameters of the IPG 115. The setting of parameters of the IPG results in a “program,” which is also referred to herein as a “protocol,” for the electrode stimulation. Programming may result in multiple protocols that the patient can choose from. Multiple protocols allows, for example, the patient to find a best setting for paresthesia at a particular time of treatment.

With reference to FIG. 3, an electrode array 120 includes eight electrodes 150B. The shown electrode array 120 has two columns and four rows as viewed along a longitude length of the lead 110. More generically, the lead includes cl columns and r rows, where cl is two and r is four. When referring to a particular column, the column is referred to herein as the j-th column, and when referring to a particular row, the row is referred to as the i-th row.

Before proceeding further, it should be understood that not all electrode arrays 120 are conveniently shaped as a simple matrix having definite columns and definite rows. More complex configurations are possible, which are referred to herein as complex electrode array configurations. The processes discussed herein can account for complex electrode array configurations. For example, a representative array having cl columns and r rows for a complex electrode array configuration may include “dummy” addresses having “null” values in the array. For a specific example, an electrode contact may span multiple columns. The resulting array may have a first address i, j representing the multiple column electrode and a second address i, j+1 having a “null” value to account for the multiple columns of the multiple column electrode. This concept can be expanded to even more complex arrangements. Accordingly, all electrode arrays 120 can be addressed as a matrix and it will be assumed herein that the electrode array 120 has been addressed as a matrix.

One process of selecting a best protocol for providing electrical stimulation includes four sub-processes. The processes are referred to herein as the impedance sweep of electrodes, the perception-threshold sweep, the pain-coverage sweep, and the parameter fine adjustment. The selecting of a best protocol occurs during a method of treating a patient with spinal cord stimulation. FIGS. 10-15 provide multiple flow diagrams relating to the treatment of the patient 105 using the SCS 100.

Before proceeding further, it should be understood that the steps discussed in connection with FIGS. 10-15 will be discussed in an iterative manner for descriptive purposes. Various steps described herein with respect to the process of FIGS. 10-15 are capable of being executed in an order that differs from the illustrated serial and iterative manner of discussion. It is also envisioned that not all steps are required as described below.

With reference to FIG. 10, the patient 105 performs an initial visit (block 500). The clinician working with the patient 105 logs into the CP 130 (block 505), and either selects a stored existing patient or adds a new patient to the CP 130 (block 510). The patient 105 then describes his pain area (block 515). Using the patient's description, implant sites for a future surgery (block 520) are determined. The patient 105 is then scheduled for trial surgery (block 525).

Referring now to FIG. 11, the patient 105 returns for trial surgery (block 530). After obtaining the previously stored patient information, the patient 105 again describes his pain area (block 535) and the location for lead implant sites can be confirmed. During the procedure, one or more leads 110 are placed in the patient 105 and their respective locations recorded in the CP 130 (block 540). Further, the camera 380 can be used to capture images of the procedure, and capture/read barcode serial numbers of the leads 110 (block 545). It also envisioned that fluoroscopy/X-ray images can be recorded in the CP 130 as part of the procedure. The result of blocks 540 and 545 is that the CP 130 has a type, location, orientation, and other contextual information relating to the implanting of the lead 110. This provides a more robust and accurate programming of the lead 110.

Next (block 550), the clinician selects the lead 121 for programming. The programming can be manual or assisted (block 555), both of which are discussed below. The process can then be repeated for a next lead, or the patient is then scheduled for post-op programming (block 560).

Referring again to block 555, the clinician either manually or automatically programs the operation of the IPG 115 (which may also be an EPG) to provide electrical stimulation through the lead 110. With manual programming (FIG. 12, block 562), the clinician selects a lead (block 563), selects a stimulation polarity, which may be cathodal stimulation as it requires the least amount of current (voltage) to elicit a response (block 564), and manually adjusts pulse amplitude, frequency, and width of the electrical stimuli provided by the electrodes 150 (block 565). The patient 105 typically provides verbal responses to cues given by the clinician. This in particular is difficult and time consuming during a permanent implant where the patient has to be woken up from the general anesthesia and struggling to be cognitive with often speech impediments. This process can be very time consuming given the number of variables for each electrode/channel. The manual process also does not often result in a “best fit” for providing electrical stimulation treatment and relies significantly on the clinician's experience. The CP 130 saves the resulting protocol of the manually assisted programming (block 570).

With assisted programming (FIG. 13, block 572), the CP 130 establishes a protocol for providing electrical stimuli to the patient 105. More specifically, the assisted programming first performs three sweeps of the electrodes 150 to result in a best selection of the electrodes 150 for providing paresthesia. The first sweep (block 575) is an impedance sweep to determine a respective impedance between the IPG 115, connected lead, each electrode 150, and tissue. The impedances are displayed on the touch screen 375 and can be used by the clinician to help determine whether an electrode 150 falls in between an accepted impedance range. The second sweep (block 580) is a perception-threshold sweep to find the minimum threshold stimulation sensed by the patient 105 for each channel/electrode 150. The second sweep (block 580) is a perception-threshold sweep to find the minimum threshold. In one implementation, the stimulation sensed by the patient 105 for each channel/electrode 150 is cathodal polarity with the IPG 115 can being the anode. For an EPG, a reference electrode may represent the cathodal anode. The values of the perception-threshold sweep are used to normalize the initial sensation felt by the patient with each electrode 150. The last sweep (block 585) is a pain-area sweep to identify the optimal paresthesia electrodes to the pain area. Even more accurately, the pain-area sweep (block 585) eliminates contacts not reaching the pain area. The clinician can then repeat any of the sweeps and/or refine the paresthesia to the patient (block 590). The refining of the paresthesia can include adjusting parameters of electric stimulation through the electrodes identified in block 585, surrounding an electrode identified in block 585 with anode or cathode blocks, or shifting a pattern longitudinally or laterally, as is known in the art. After completion, the CP 130 saves the stimulation parameters (block 595). Further discussion regarding the CP 130 assisted programming will be provided below.

Before proceeding further, it should be noted that the contextual information relating to the implanting of the lead 110 (from blocks 540 and 545, above) can be used when programming the stimulation generator. That is, the contextual information can be used to exactly identify the lead 110, corresponding electrode array 120, orientation of the lead 110, the placement of the lead 110, etc. The CP 130 automatically accounts for this information when establishing the protocol. For a specific example, the CP allows for an anatomically correct placement of the stimulation lead, if the surgeon chooses to orient the lead in another way, such as antegrate or diagonal. The CP 130 accounts for this placement while performing the sweeps.

Referring now to FIG. 14, the patient 105 returns for post operation programming (block 600). Again, the patient 105 can describe the pain he is experiencing (block 605). The clinician then selects a lead 110 for programming (block 610) and performs manual or assisted programming for the lead 110 (block 615). The patient is then scheduled for permanent surgery (block 620).

With permanent surgery (FIG. 15, block 630), the operation is similar to the trial surgery except the IPG 115 is typically inserted into the patient. At block 635, the patient again describes his pain area (block 635), which typically corresponds to the previously described pain area, and the location for lead implant sites can be confirmed. During the procedure, one or more leads 110 are placed in the patient and recorded in the CP (block 640). Also, the IPG 115 is placed in the patient and recorded in the CP 130 (block 640). The camera 380 can be used to capture images of the procedure, capture/read barcode serial numbers of the leads 110, and capture/read barcode serial numbers of the IPG (block 645). Further, fluoroscopy/X-ray images can be recorded in the CP 130, similar to the trial surgery, to help record the procedure (block 645). Next (block 650), the clinician selects the lead 110 for programming. The programming can be manual or assisted (block 655), as already discussed. The process can then be repeated for a next lead 110.

Accordingly, FIGS. 11-15 provide a process for treating a patient using the SCS 100. FIGS. 16-19 provide more detailed processes for performing computer assisted stimulation programming (CASP) using the CP 130. The steps discussed in connection with FIGS. 16-19 will be discussed in an iterative manner for descriptive purposes. Various steps described herein with respect to the process of FIGS. 16-19 are capable of being executed in an order that differs from the illustrated serial and iterative manner of discussion. It is also envisioned that not all steps are required as described below.

FIG. 16 shows four exemplary sub-processes of the CASP process. The first process (block 675) retrieves impedance values of the electrodes 150 in a lead 110. In order to perform the process 675, the clinician identifies the lead 110 to the CP 130. The CP 130 knows the arrangement of the electrode array 120, as previously discussed, for the lead 110 once the lead 110 is identified. One exemplary pseudo code and related flow chart for process 675 is shown below and in FIG. 17, respectively. This pseudo code assumes impedance between the contact Z_(i,j), connected lead, the can of the IPG 115, and tissue. However, other impedance combinations are possible between contacts Z_(i,j) and Z_(k,l),

where (k=1:r); (l=1:cl) and (k!=i) v (l!=j);

Require: EPG or IPG communication established  1: [Z_(i,j)] ← 0 >setting impedance array to zero 2: r ← number of rows >number of contacts in lead latitudinally 3: cl ←number of columns > number of contacts in lead longitudinally 4: for j = 1 to ≦ cl do 5: for i = 1 to ≦ r do 6: Z_(i,j) ← retrieve impedance of contact i, j >computed by IPG/EPG 7: end for 8: end for 9: return [Z_(i,j)]

First, the array [Zi,j] is set to zero, the number of rows r is identified, and the number of columns cl is identified (block 695). The array [Zi,j] corresponds to an array representing the electrode array 120. The letter i represents the i-th row from 1 to r rows. The letter j represents the j-th column from 1 to j columns. As discussed previously, the representative array [Zi,j] can represent many electrode arrays, including complex electrode array configurations having “dummy” addresses with “null” values. Therefore, not every address of the array [Zi,j] may include a value. Returning to FIG. 17, the process performs a first for-loop (block 700) for the columns and a second for-loop (block 705) for the rows of the array [Zi,j]. The two loops allow the process to progress through each electrode 150 of the electrode array 120 to obtain an impedance value associated with each channel (block 710). Each impedance value relates to the impedance between the can 220 of the IPG 115, the connected lead, tissue, for example, and a respective electrode 150. The process of FIG. 17 helps to determine that the impedance values of lead 110 fall within acceptable ranges, necessary to provide electrical stimulation to the nerves.

Referring back to FIG. 16, the second process (block 680) determines the perception-threshold values of the electrodes 150 in a lead 110. During the process, the patient 105 provides feedback using the PFD 145 when the patient 105 senses a stimulation, such as a paresthesia sensation. One exemplary pseudo code and related flow chart for process 680 is shown below and in FIG. 18, respectively.

Require: EPG or IPG communication established Ensure: Impedance of each contact retrieved  1: [Cthr_(i,j)] ← 0 >setting contact stim threshold array to zero  2: r ← number of rows >number of contacts in lead latitudinally  3: cl ← number of columns >number of contacts in lead longitudinally  4: stimAmpStart ← sA_(start) >initial stim amplitude  5: stimAmpEnd ← sA_(end) >ending stim amplitude  6: stimAmpInc ← sInc >stim amplitude increment  7: stimAmp ← stimAmpStart >beginning stimulation amplitude  8: setSweepFrequencyForward  >activation frequency  9: setStimFrequency >stimulation in pulses per seconds 10 setStimDuration >duration of stimulation per contact 11: contactCounter ← 0 12: Camp_(ij) ← 0 13: while stimAmp ≦ stimAmpEnd && contactCounter ≦ totalContacts do 14:  for j = 1 to cl do 15: for i = 1 to r do 16:  if Cthr_(i,j) ≠ 0 then >ignore contacts that already have thresholds established 17: continue 18:  end if 19: listenForPatientResponse( ) 20:  Camp_(i,j) ←stimAmp for stimDuration >start stimulation 21:  if patientResponded then 22: setSweepFrequencyReverse, startSweepReverse 23: for revJ = j downto revJ > 0 do 24: for revI = i downto revI > 0 do 25: if Cthr_(revI,revJ) ≠ 0 then>ignore contacts that already have thresholds established 26:  continue 27: end if 28: Camp_(revI,revJ) ← stimAmp for stimDuration > start stimulation 29: if patientResponded then 30:  Cthr_(revI,revJ) ← Camp_(revI,revJ) 31:  contactCounter ++ 32: endif 33:  end for 34: end for 35:  end if 36:  setSweepFrequencyForward 37: end for 38: end for 39:  stimAmp+←stimAmlnc 40: end While 41: return [Cthr_(i,j)]

First the array [Cthr_(i,j)] is set to zero, the number of rows r is identified and the number of columns cl is identified (block 720). Also, the initial stimulation amplitude stimAmpStart, the ending stimulation amplitude stimAmpEnd, and the stimulation amplitude increment stimAmpInc are identified; the variable stimAmp is set; and the counter contactCounter is set. Also, the forward sweep frequency setSweepFrequencyForward, the stimulation frequency setStimFrequency, the duration of stimulation setStimDuration are established and the stimulation Camp_(ij) is tuned off (block 720).

The CASP process performs a while-loop to determine the perception-threshold values of the electrodes 150. The while-loop is performed while the stimAmp value is less than the threshold stimAmpEnd and each contact does not have a perception-threshold value (block 724). The while-loop includes two for-loops: a first for-loop for the columns of the array (block 728) and a second for-loop for the rows of the array (block 732). The two loops allow the CASP process to progress through each electrode 150 of the electrode array 120. While performing the loops, the process determines whether the perception array does not have a perception value for the i-th row and the j-th column (block 736). If the array location has a perception-threshold value, then the process returns to block 732. Otherwise, the process continues.

Before proceeding further, it should be noted that the CASP process automatically and systematically progress through the electrodes 150. In addition, as shown by block 736, the CASP process “skips” or passes over an electrode C_(i,j) once a perception threshold Cthr_(i,j) is identified for the electrode 150. However, the sweeping of the electrodes 150 is still automated and systematic even when this skip process occurs.

Referring now to block 740, the contact amplitude Camp_(i,j) is set to the stimulation amplitude stimAmp, the process pauses for a duration. At the same time the CASP is monitoring for a patient response. For the implementation discussed herein, the stimulation amplitude is a current amplitude. However, a voltage amplitude or other variable (pulse shape, frequency, width, etc.) can be used and adjusted in place of the current amplitude. If the patient 105 feels a sensation, then they provide feedback to the CP 130 via the PFD 145 (block 744). If a patient 105 response is detected then the process proceeds to block 748. Otherwise, the CASP process continues to proceed through the for-loops.

When a patient 105 provides feedback indicating a response, a reverse frequency is set (block 748) and the sweep is reversed (starting at block 752). More specifically, for the CASP process discussed herein, the process proceeds quickly through the electrode array 120 and a delayed reaction from the patient 105 is expected. By performing a reverse sweep, the CASP process more accurately confirms a response. The CASP process initiates two for-loops 752-756 in a reverse sweep direction. While performing the reverse sweep, the process “skips” or passes over electrodes 150 having perception thresholds (block 760). The contact amplitude Camp_(revI,revJ) is set to the stimulation amplitude stimAmp, the process pauses for a duration (block 764). If a patient 105 feels a sensation, then they provide feedback to the CP 130 with the PFD 145. If a patient 105 response is detected (768), then the process proceeds to block 772. Otherwise, the CASP process continues to proceed through the for-loops 752 and 756. At block 772, the perception-threshold value is set for Cthr_(revI,revJ) and the contactCounter increments.

Upon completion of the perception threshold sweep, perception thresholds [Cthr_(i,j)] are established for each contact 150. The values of the perception-threshold sweep are used to normalize the initial sensation felt by the patient with each channel/electrode 150.

Referring again to FIG. 16, the third process (block 685) performs a pain-area sweep to determine the best electrode(s) 150 for stimulating neurons to the affected pain area. During this process, the patient 105 again provides feedback using the PFD 145 when the patient 105 senses a defined stimulation. One exemplary pseudo code and related flow chart for process 685 is shown below and in FIG. 19, respectively.

Require: [Cthr_(i,j)] ≠ 0 >threshold array is not empty Ensure: stimulation contacts that cover pain  1: [Parea_(i,j,k)] ← false  2: setSweepFrequencyForward >activation frequency  3: setStimFrequency  >stimulation in pulses per seconds  4: setStimDuration >duration of stimulation per contact  5: r ← number of rows >number of contacts in lead latitudinally  6: cl ← number of columns >longitudinal columns  7:  for: j = 1 to ≦ r do  8:  for i = 1 to ≦ cl do  9: listenForPatientResponse( ) 10: Camp_(i,j) ← Cthr_(i,j) for stimDuration >start stimulation 11: if patientResponse then 12:  k ← patientPainRegion > patient locates where pain  region is 13:  PainA_(i,j,k) ← true 14: end if 15:  end for 16: end for 17: return [Parea_(i,j,k)]

First, the forward sweep frequency setSweepFrequencyForward, the stimulation frequency setStimFrequency, the duration of stimulation setStimDuration are established and the stimulation Camp_(ij) is tuned off (block 800). Next, the number of rows r is identified, the number of columns cl is identified, and the array [Pareai_(j,k)] is set to false (block 802). The CASP process then automatically and systematically progresses through the electrodes 150. A first for-loop (block 805) for the columns of the area and a second for-loop (block 810) for the rows of the array are swept. While performing the loops, the electrode Camp, is set to the threshold Cthr_(i,j), which may be set from the prior perception-threshold sweep (block 815). The process pauses for a duration. If the electrode 150 stimulates neurons related to the pain area, then the patient 105 provides feedback to the CP 130 via the PFD 145. If a patient 105 response is detected (block 820) then the process proceeds to block 825. Otherwise, the CASP process continues the automated and systematic sweep through the electrodes 150. At block 825, the patient identifies the paresthesia area (k) the stimulation is reaching and contact i,j in the array [Parea_(i,j,k)] is set to true.

In some implementations, when a patient 105 provides feedback indicating a response to the stimulation that reaches the pain area, the sweep can be repeated multiple times over. The resulting multitude pain area arrays can be compared to verify consistent patient response. However, the exemplary process shown in FIG. 19 does not include the repeated sweep.

At the end of the pain-area sweep, the CP 130 identifies the best electrode(s) 150 for stimulating neurons to the affected pain area, i.e., to provide paresthesia to the affected pain areas. It is envisioned that the process of performing the perception threshold sweeps and pain area sweeps can be performed in less than thirty minutes, and preferably in less than ten minutes. The time can vary based on the sweep speed and delay times used during the sweep. The CP 130 can then isolate the resulting best electrodes and refine the stimulation parameters (amplitude, frequency, pulse width) to result in an optimal pattern as has been previously done in prior SCS systems (block 690 of FIG. 16).

Thus, the invention provides, among other things, useful and systems and methods for providing electrical stimulation to a neural tissue of a patient. Various features and advantages of the invention are set forth in the following claims. 

What is claimed is:
 1. An electronic apparatus for performing a computer-assisted stimulation programming of an implantable medical device, the electronic apparatus comprising: an electronic patient feedback device configured to generate signals in response to a voluntary tactile or visual engagement from a patient; a first programming device configured to offer a first set of programming options for programming the implantable medical device; and a second programming device configured to offer a second set of programming options for programming the implantable medical device, wherein the second set of programming options is greater than the first set of programming options, and wherein the second programming device includes: a user interface configured to receive user input; a memory storage component configured to store programming code; and a computer processor configured to execute the programming code to perform the following operations: determining a perception threshold for each of a plurality of contacts on a lead that is configured to be implanted inside the patient, wherein the determining comprises, determining, for each of the contacts, a respective minimum stimulation parameter that causes the patient to sense an electrical stimulation; thereafter determining a paresthesia coverage for each of the plurality of contacts by automatically and steadily incrementing, for each of the contacts, a stimulation parameter from a respective starting value that is set to the perception threshold for said contact; identifying, based on the determining of the paresthesia coverage, a subset of the contacts that offer paresthesia coverage for a pain area of the patient; and performing, in response to the user input received through the user interface, stimulation programming using the subset of the contacts; wherein the determining the perception threshold or the determining the paresthesia coverage is performed at least in part based on the signals generated by the electronic patient feedback device.
 2. The electronic apparatus of claim 1, wherein the operations further comprise, before the determining the perception threshold: measuring an impedance for each of the plurality of contacts; and determining which contacts have connections problems based on the measured impedance.
 3. The electronic apparatus of claim 1, wherein: the determining of the perception threshold and the determining the paresthesia coverage each comprises executing a respective sweep using a nested loop structure.
 4. The electronic apparatus of claim 1, wherein: the determining of the perception threshold comprises automatically incrementing a value of the stimulation parameter by one predetermined step size at a time until a patient feedback indicating perceived stimulation by the patient is received via the electronic patient feedback device.
 5. The electronic apparatus of claim 1, wherein: the determining of the paresthesia coverage comprises automatically incrementing a value of the stimulation parameter by one predetermined step size at a time until a patient feedback indicating perceived paresthesia by the patient is received via the electronic patient feedback device.
 6. The electronic apparatus of claim 1, wherein the electronic patient feedback device generates the signals in response to a squeezing of a housing of the electronic patient feedback device.
 7. A medical system, comprising: a lead configured to deliver electrical stimulation to a patient via one or more of a plurality of contacts located on the lead; a pulse generator to which the lead is coupled, wherein the pulse generator is configured to generate the electrical stimulation; a patient programmer device configured to program the pulse generator; an electronic patient feedback device that includes one or more sensors, wherein the electronic patient feedback device is configured to produce an electronic patient feedback signal in response to a voluntary tactile or visual engagement by the patient, the electronic patient feedback device being different from the patient programmer device; and a clinician programmer device different from the patient programmer device, the clinician programmer being coupled to the pulse generator and to the electronic patient feedback device, wherein the clinician programmer device is configured to program the pulse generator to generate the electrical stimulation, and wherein the clinician programmer device includes: a memory storage component configured to store computer instructions; and a processor component configured to execute the computer instructions; wherein the computer instructions, when executed by the processor component, perform the following operations: determining a perception threshold for each of the plurality of contacts, wherein the determining comprises determining, for each of the contacts, a respective minimum stimulation parameter that causes the patient to sense an electrical stimulation; thereafter determining a paresthesia coverage for each of the plurality of contacts by automatically and steadily incrementing, for each of the contacts, a stimulation parameter from a respective starting value that is set to the perception threshold for said contact; identifying, based on the determining of the paresthesia coverage, a subset of the contacts that offer paresthesia coverage for a pain area of the patient; and performing, in response to user input, stimulation programming using the subset of the contacts.
 8. The medical system of claim 7, wherein the operations further comprise, before the determining the perception threshold: measuring an impedance for each of the plurality of contacts; and determining which contacts have connections problems based on the measured impedance.
 9. The medical system of claim 7, wherein: the determining of the perception threshold and the determining the paresthesia coverage each comprises executing a respective sweep using a nested loop structure.
 10. The medical system of claim 7, wherein: the determining of the perception threshold comprises automatically incrementing a value of the stimulation parameter by one predetermined step size at a time until a patient feedback indicating perceived stimulation by the patient is received via the electronic patient feedback device.
 11. The medical system of claim 7, wherein: the determining of the paresthesia coverage comprises automatically incrementing a value of the stimulation parameter by one predetermined step size at a time until a patient feedback indicating perceived paresthesia by the patient is received via the electronic patient feedback device.
 12. The medical system of claim 7, wherein the electronic patient feedback device is configured to produce the electronic patient feedback signal in response to a pressure applied by the patient on a housing of the electronic patient feedback device.
 13. The medical system of claim 7, wherein the electronic patient feedback device produces the electronic patient feedback signal in response to a squeezing of a housing of the electronic patient feedback device.
 14. A method of performing a computer-assisted stimulation programming of an implantable medical device, the method comprising: determining, via a clinician programming device, a perception threshold for each of a plurality of contacts on a lead that is configured to be implanted inside a patient, wherein the determining comprises, determining, for each of the contacts, a respective minimum stimulation parameter that causes the patient to sense an electrical stimulation, and wherein the clinician programming device is different from, and offers more programming options than, a patient programming device; thereafter determining, via a clinician programming device, a paresthesia coverage for each of the plurality of contacts by automatically and steadily incrementing, for each of the contacts, a stimulation parameter from a respective starting value that is set to the perception threshold for said contact; identifying, via a clinician programming device and based on the determining the paresthesia coverage, a subset of the contacts that offer paresthesia coverage for a pain area of the patient; and performing, via a clinician programming device and in response to user input, stimulation programming using the subset of the contacts; wherein the determining the perception threshold or the determining the paresthesia coverage is performed at least in part based on signals generated by an electronic patient feedback device in response to a voluntary tactile or visual engagement from the patient, the electronic patient feedback device being different from the patient programming device and the clinician programming device and including a pressure sensor to sense a variable force applied by the patient as the voluntary tactile engagement.
 15. The method of claim 14, further comprising, before the determining the perception threshold: measuring an impedance for each of the plurality of contacts; and determining which contacts have connections problems based on the measured impedance.
 16. The method of claim 14, wherein: determining of the perception threshold and the determining the paresthesia coverage each comprises executing a respective sweep using a nested loop structure.
 17. The method of claim 14, wherein: the determining of the perception threshold comprises automatically incrementing a value of the stimulation parameter by one predetermined step size at a time, until a patient feedback indicating perceived stimulation by the patient is received via the electronic patient feedback device; and the determining of the paresthesia coverage comprises automatically incrementing a value of the stimulation parameter by one predetermined step size at a time until a patient feedback indicating perceived paresthesia by the patient is received via the electronic patient feedback device.
 18. The method of claim 14, wherein: the signals generated by the electronic patient feedback device comprise an analog signal, and wherein the method further comprises converting the analog signal into a digital signal.
 19. The method of claim 14, wherein the determining the perception threshold and the determining the paresthesia coverage are performed during a surgical setting where the patient is woken up from anesthesia.
 20. The method of claim 14, wherein the pressure sensor includes a strain gauge, and wherein the variable force is applied by a squeezing of a housing of the electronic patient feedback device. 